Methods of particle manipulation and analysis

ABSTRACT

Methods described herein, in some embodiments, permit extraction of particle structural and/or surface charge data from gradient induced particle motion in channels. In one aspect, a method of manipulating particle motion comprises introducing a fluid into a channel, the fluid comprising particles, and driving particle accumulation to a preselected location in the channel by setting advective velocity of the fluid to offset diffusiophoretic mobility of the particles at the preselected location.

RELATED APPLICATION DATA

The present application claims priority pursuant to 35 U.S.C. § 119(e)to U.S. Provisional Patent Application Ser. No. 62/594,871 filed Dec. 5,2017 and U.S. Provisional Patent Application Ser. No. 62/682,449 filedJun. 8, 2018, each of which is incorporated herein by reference in itsentirety.

STATEMENT OF GOVERNMENT RIGHTS

This invention was made with government support under Grant No.DE-AC05-00OR22725 awarded by the Department of Energy and Award No.CBET1702693 awarded by the National Science Foundation. The governmenthas certain rights in the invention.

FIELD

The present invention relates to methods of particle manipulation andanalysis and, in particular, to methods employing solute gradients forparticle manipulation and analysis.

BACKGROUND

Particle motion or transport in suspensions and colloids is important inmany applications including drug delivery, disinfection, filtration andfluid sample analysis. Several mechanisms exist to induce directedmotion of colloidal particles, such as employment of one or moreexternal forces. External forces can include electrostatic, dielectric,magnetic, acoustic, optical and/or inertial effects. Effectiveapplication of external forces can necessitate apparatus of complexarchitecture and design. Additionally, use of external forces oftenfails to reveal meaningful information of particle systems, such as zetapotential and particle size.

SUMMARY

In view of the foregoing deficiencies, new methods of particlemanipulation and analysis are needed. Methods described herein, in someembodiments, permit extraction of particle structural and/or surfacecharge data from gradient induced particle motion in channels. In oneaspect, a method of manipulating particle motion comprises introducing afluid into a channel, the fluid comprising particles, and drivingparticle accumulation to a preselected location in the channel bysetting advective velocity of the fluid to offset diffusiophoreticvelocity of the particles at the preselected location. In someembodiments, fluid advective velocity and diffusiophoretic velocity ofthe particles are equal or substantially equal, resulting in cessationof particle movement in the fluid at the preselected location. In otherembodiments, the difference between fluid advective velocity andparticle diffusiophoretic velocity is sufficiently small, therebypermitting particle accumulation at the preselected location for adefined period of time. Additionally, non-accumulated particles can bepassed out of the channel by the advective velocity of the fluid.

In another aspect, methods of particle separation are described. Amethod of particle separation comprises introducing a fluid into achannel, the fluid comprising a mixture of particle species. Theparticle species are separated in the fluid by driving accumulation ofthe particle species to preselected locations in the channel via settingadvective velocity of the fluid to offset diffusiophoretic velocity of aparticle species at each of the preselected locations. In someembodiments, one or more of the separated particle species can beanalyzed or characterized in the channel. Moreover, one or more of theseparated particle species can be selectively removed from the channel.

In another aspect, methods of particle analysis are described. A methodof particle analysis comprises introducing a fluid into a channel anddetermining the presence of analyte particles in the fluid sample bydriving accumulation of the analyte particles to a preselected locationin the channel. The analyte particles are driven to the preselectedlocation by setting advective velocity of the fluid sample to offsetdiffusiophoretic velocity of the analyte particles at the preselectedlocation. The presence of the analyte particles at the preselectedlocation is subsequently detected. In other embodiments, a method ofparticle analysis comprises introducing a fluid sample into a channel.The presence of a plurality of analyte particle species in the fluidsample is determined by driving accumulation of the analyte particlespecies to preselected locations in the channel. The analyte particlespecies are driven by setting advective velocity of the fluid to offsetdiffusiophoretic velocity of an analyte particle species at each of thepreselected locations. The presence of the analyte particles at each ofthe preselected locations is then detected.

In a further aspect, methods of determining particle zeta potential aredescribed. A method of determining particle zeta potential, in someembodiments, comprises introducing a fluid into a channel, the fluidhaving an advective velocity and solute concentration gradient.Particles are introduced into the fluid and accumulated at a location inthe channel where the advective velocity of the fluid is offset bydiffusiophoretic velocity of the particles. The diffusiophoreticmobility of the particles is calculated from this location in thechannel, and the particle zeta potential is derived from thediffusiophoretic mobility.

In other embodiments, a method of determining particle zeta potentialcomprises providing at least one dead-end pore containing solute havinga first solute concentration and introducing a plurality of colloidalparticles into the dead-end pore, the colloidal particles havingpositive diffusiophoretic mobility and a second solute concentrationless than the first solute concentration. The image intensity in thedead-end pore is measured, and the maximum colloidal density isdetermined based on the image intensity. Particle zeta potential isderived from the maximum colloidal density. In some embodiments, theimage intensity is measured after migration of the colloidal particlesin the dead-end pore reaches a quasi-steady state.

In another aspect, methods of determining the zeta potential of channelsurfaces and/or walls are described. In some embodiments, a method ofdetermining surface or wall zeta potential comprises providing at leastone dead-end pore containing a solute having a first soluteconcentration and introducing a plurality of colloidal particles havinga second solute concentration less than the first solute concentration.The plurality of colloidal particles migrate into the dead-end pore, andthe image intensity of the dead-end pore is measured prior to thecolloidal particle migration reaching a quasi-steady state. Thetransient peak position is determined from the image intensity, and zetapotential of the pore wall is determined from the transient peakposition. In some embodiments, wall zeta potential is determined byfitting the transient peak position to a power law curve, obtaining apower law exponent, and comparing the effective power law exponent toresults from a two-dimensional computer simulation.

In another aspect, methods of determining the zeta potential of channelwalls or surfaces via pressure measurements are described. A method ofdetermining zeta potential of channel walls or surfaces, in someembodiments, comprises establishing a solute concentration gradient toinduce a wall slip boundary condition in the channel. The pressure dropalong the channel is measured, and channel wall diffusiophoreticmobility of the slip boundary condition is derived from the measuredpressure drop. The zeta potential of the channel walls or surfaces isderived from this wall diffusiophoretic mobility. In some embodiments,for example, the wall diffusiophoretic mobility is derived from arelation between the measured pressure drop and the wall slip velocityof the boundary condition.

Zeta potentiometers are also described herein. In some embodiments, azeta potentiometer comprises at least one flow channel, at least onelight source for illuminating the flow channel, and an imaging devicepositioned to observe the illuminated flow channel. A sample storagelocation is adapted to provide a sample to the at least one flow channelfor analysis.

These and other embodiments are further described in the followingdetailed description.

BRIEF DESCRIPTION OF THE DRAWINGS

FIGS. 1A-C illustrate principles of particle manipulation according tosome embodiments described herein.

FIG. 2 illustrates peak particle concentration location (x_(p)) in thechannel as a function of solute Peclet number for a variety ofdiffusiophoretic mobilities (Γ_(p)/D_(s)) according to some embodiments.

FIG. 3 illustrates suspended concentration profiles for particles withdiffering diffusiophoretic mobilities according to some embodiments.

FIG. 4A illustrates introduction of colloidal particles with soluteconcentration c_(o) in a dead-end pore that initially contains highersolute concentration c_(i).

FIG. 4B illustrates migration of the colloidal particles into the porevia diffusiophoresis.

FIG. 4C illustrates the condition after solute equilibration across thepore where the quasi-steady state location of the maximum colloidaldensity (x_(m) ^(∞)) is determined from the experimental image intensity(I).

FIG. 4D illustrates particle zeta potential ζ_(p) as a function of x_(m)^(∞).

FIG. 5A illustrates colloid particle migration into a dead-end poreinduced by solute gradients.

FIG. 5B illustrates the corresponding fluorescence intensitydistribution of the colloidal particles migrating into the dead-endpore.

FIG. 5C illustrates the normalized location of the maximum intensity(x_(m)/L) over time.

FIG. 5D is an image sequence of time-dependent colloidal particledistribution in the dead-end pore.

FIG. 5E illustrates the cross-section averaged colloidal particledensity distribution in the dead-end pore normalized by the maximumdensity (n/n_(m) ^(∞)) at 300 s.

FIG. 5F illustrates the maximum intensity distribution over time using3D, 2D, and 1D-simulation results.

FIG. 6 illustrates 1D-simulations of maximum intensity location(x_(m)/L) over time for ζ_(p) ranging from −40 mV-100 mV with a step of10 mV. The inset indicates x_(m) ^(∞)/L at 300 s versus ζ_(p), where thedashed curve corresponds to 1D-simulation results and the solid curvescorrespond to 2D-simulation results.

FIG. 7A illustrates particle trajectories in the presence ofdiffusioosmotic flow induced by nonzero wall zeta potential ζ_(w).

FIG. 7B illustrates a 2D simulation of particle distribution in achannel with wall slip flow.

FIG. 7C illustrates a 2D simulation of particle distribution in achannel without wall slip flow.

FIG. 7D provides 2D numerical results of x_(m)/L over time plotted inlog-log scale for various ζ_(w) (−20 to −80 mV) with ζ_(p) of −80 mV.The dashed curve represents 1D results, which neglect fluid flow. Theinset is β versus ζ_(w) at early times (t<60 s) for a wide range ofζ_(p,w) values.

FIG. 7E illustrates a comparison of colloidal particle migration in bareand plasma treated PDMS channels. The scale bar is 50 μm.

FIG. 7F illustrates corresponding particle peak locations over time inthe plasma treated and untreated channels of FIG. 7e . The curve in theinset indicates β versus ζ_(w) with ζ_(p)=−80 mV.

FIGS. 8A and 8B illustrate a system setup for determining wall zetapotential of a channel via pressure measurements, wherein ends of thechannel are coupled to larger main channels.

FIG. 9 illustrates a system design for measuring zeta potential ofchannel walls or surfaces according to some embodiments.

FIG. 10 illustrates a zeta potentiometer according to some embodiments.

DETAILED DESCRIPTION

Embodiments described herein can be understood more readily by referenceto the following detailed description and examples and their previousand following descriptions. Elements, apparatus and methods describedherein, however, are not limited to the specific embodiments presentedin the detailed description and examples. It should be recognized thatthese embodiments are merely illustrative of the principles of thepresent invention. Numerous modifications and adaptations will bereadily apparent to those of skill in the art without departing from thespirit and scope of the invention.

In one aspect, methods of manipulating particle motion are provided. Amethod of manipulating particle motion comprises introducing a fluidinto a channel, the fluid comprising particles, and driving particleaccumulation to a preselected location in the channel by settingadvective velocity of the fluid to offset diffusiophoretic velocity ofthe particles at the preselected location. In some embodiments, fluidadvective velocity and diffusiophoretic velocity of the particles areequal or substantially equal, resulting in cessation of particlemovement in the fluid at the preselected location. In other embodiments,the difference between fluid advective velocity and particlediffusiophoretic velocity is sufficiently small, thereby permittingparticle accumulation at the preselected location for a defined periodof time. Additionally, non-accumulated particles can be passed out ofthe channel by the advective velocity of the fluid.

As detailed herein, diffusiophoretic velocity of the particles is afunction of particle size, particle surface charge, strength of thesolute gradient in the fluid and/or various combinations thereof. Inparticular, diffusiophoretic velocity is equal to the product ofparticle diffusiophoretic mobility (Γ_(p)) and gradient log soluteconcentration, u_(dp)=Γ_(p)∇ln c. In some embodiments, the solutegradient is established by connecting the channel with a second channeltransporting fluid having a differing solute concentration. FIGS. 1A-Cillustrate principles of particle manipulation according to someembodiments described herein. As illustrated in FIG. 1A, a side channel10 containing particles is in fluid communication with a second or mainchannel 11. The solute concentration in the fluid of the side channel 10differs from the solute concentration in the main channel 11, therebyestablishing a solute gradient in the side channel 10. Inside the sidechannel 10, particle motions are governed by a combination of the fluidvelocity (u_(f)) and the diffusiophoretic velocity (u_(dp)) resultingfrom the solute concentration gradient. With appropriately chosenparameters for the particles of interest, the fluid and diffusiophoreticvelocities can be designed to act in opposite or offsetting directions,resulting in a stable position in the pore (x_(p)) where particles canaccumulate. The location of the site of accumulation can be preselectedby knowing the diffusiophoretic velocity of the particles and settingthe fluid velocity to offset the diffusiophoretic velocity at thepreselected location. Equation (1), for example, can be employed in someembodiments to select one or more particle accumulation sites (x_(p)) inthe channel.

$\begin{matrix}{x_{P} = {{Pe}_{s}^{- 1}\mspace{14mu}{\ln\left\lbrack \frac{\beta - e^{{Pe}_{s}}}{\left( {1 + \frac{\Gamma_{p}}{D_{s}}} \right)\left( {\beta - 1} \right)} \right\rbrack}}} & (1)\end{matrix}$where Pe_(s) is the Peclet number, β is solute concentration at thechannel outlet, c(1, y, t), and D_(s) is solute diffusivity.Alternatively, depending on various underlying assmumptions, otherequation(s) may be used for determining one or more particleaccumulations sites (x_(p)) according to methods described herein. Insome embodiments, the fluid velocity can be set to flow particles not ofinterest out of the channel, thereby isolating particles of interest inthe channel. Subsequent to accumulation at a location in the channel,the particles can be characterized and/or selectively removed from thechannel. The particles, for example, may be characterized by one or morespectroscopic techniques, in some embodiments.

Any desired particle type or species not inconsistent with theprinciples of the present invention can be employed with methodsdescribed herein. In some embodiments, the particles are colloidal orotherwise suspended in the fluid. Particles may include chargedinorganic particles and/or charged organic particles, such as polymericparticles. In other embodiments, particles comprise one or morebiomolecular species including, but not limited to, small moleculedrugs, nucleic acids, proteins, vesicles and pathogens such as viruses,bacterial and other microbial species. Particles may also compriseemulsions.

In another aspect, methods of particle separation are provided. A methodof particle separation comprises introducing a fluid into a channel, thefluid comprising a mixture of particle species. The particle species areseparated in the fluid by driving accumulation of the particle speciesto preselected locations in the channel via setting advective velocityof the fluid to offset diffusiophoretic velocity of a particle speciesat each of the preselected locations. In some embodiments, one or moreof the separated particle species can be analyzed or characterized inthe channel. Moreover, one or more of the separated particle species canbe selectively removed from the channel. FIG. 2 illustrates peakparticle concentration location (x_(p)) in the channel as a function ofsolute Peclet number for a variety of diffusiophoretic mobilitiesΓ_(p)/D_(s), where Γ_(p) is diffusiophoretic mobility and D_(s) is thesolute diffusivity. As illustrated in FIG. 2, particles with differingdiffusiophoretic mobilities can be driven to differing locations in thechannel according to offsetting interaction with the fluid advectionvelocity. With reference to Equation (1) herein, for a givenΓ_(p)/D_(s), both solute Peclet number and can be tuned to selectivelydetermine the channel position at which particles accumulate. Note thatfor x_(p)<0, particle diffusiophoresis is too strong relative to fluidadvection, and particles will be continuously pumped upstream withoutaccumulating in the channel.

FIG. 3 illustrates suspended concentration profiles for particles withdiffering diffusiophoretic mobilities according to some embodiments. Ascan be seen, particles with larger Γ_(p)/D_(s) experiencediffusiophoresis more strongly and are able to propagate furtherupstream towards the channel inlet. As time progresses, particlescontinue to focus at separate locations, and particle concentrationswill continue to grow in the separate locations. Another way tointerpret the results of FIG. 3 is to consider a channel simultaneouslyfilled with uniform dilute concentrations of five different types ofparticles with the values Γ_(p)/D_(s) specified in the figure. Due tothe combined influences of fluid advection and diffusiophoresis, as timepasses, the particle concentration will begin to separate and focus atdifferent locations, forming distinct concentration peaks, effectivelysorting and focusing each of the particles based on their Γ_(p)/D_(s).For example, since the peak concentration locations are steady in timeafter an initial transient time t=O(1), and those locations are uniquelydetermined by the system parameters Pe_(s), Γ_(p)/D_(s), and β, it isstraightforward to establish Γ_(p) of the particles. In a microfluidicexperiment with fixed β and Pe_(s), the position of peak concentration(x_(p)) with unknown Γ_(p) can be measured. The unknown diffusiophoreticmobility, in some embodiments, can subsequently be directly calculatedfrom Equation (2):

$\begin{matrix}{\Gamma_{p} = {D_{s}\left( {\frac{\beta - e^{{Pe}_{s}}}{e^{{Pe}_{s}x_{p}}\left( {\beta - 1} \right)} - 1} \right)}} & (2)\end{matrix}$This configuration, therefore, has potential applications ranging fromparticle sorting, separation, and focusing, to diagnostic andmeasurement applications. In some embodiments, fluid advective velocityand diffusiophoretic velocity of the particles are equal orsubstantially equal resulting in cessation or suspension of particlemovement in the fluid at one or more channel locations. In otherembodiments, the difference between fluid advective velocity andparticle diffusiophoretic velocity is sufficiently small, therebypermitting particle accumulation at the preselected location for aperiod of time.

In another aspect, methods of particle analysis are described. A methodof particle analysis comprises introducing a fluid into a channel anddetermining the presence of analyte particles in the fluid sample bydriving accumulation of the analyte particles to a preselected locationin the channel. The analyte particles are driven by setting advectivevelocity of the fluid sample in the channel to offset diffusiophoreticvelocity of the analyte particles at the preselected location. Thepresence of the analyte particles at the preselected location issubsequently detected. In some embodiments, the fluid sample comprises aplurality of analyte particle species. In such embodiments, the presenceof analyte particle species is determined by driving accumulation of theanalyte particle species to preselected locations in the channel viasetting advective velocity of the fluid in the channel to offsetdiffusiophoretic velocity of an analyte particle species at each of thepreselected locations. The presence of the analyte particles at each ofthe preselected locations is then detected.

In the present methods of particle analysis, advective fluid velocityand solute gradients can be selected to isolate particles of interest ina fluid sample. For example, an investigator can determine or classifyparticles of interest based on their diffusiophoretic velocities.Advective fluid velocity is then selected, such that any particleshaving the desired diffusiophoretic velocities are isolated in thechannel at one or more locations. According to the principles describedherein, the location(s) of particle isolation are calculated based onfluid advective velocity and diffusiophoretic velocity. Particles notexhibiting diffusiophoretic velocities of interest can pass out of thechannel or be isolated at another location in the channel. In this way,particles of interest in an unknown sample can be isolated andidentified and/or characterized. One of more species of isolatedparticles may also be selectively removed from the channel.

In a further aspect, methods of determining particle zeta potential aredescribed. In some embodiments, a method of determining particle zetapotential comprises introducing a fluid into a channel, the fluid havingan advective velocity and solute concentration gradient. The particlesare accumulated at a location in the channel where the advectivevelocity of the fluid is offset by diffusiophoretic velocity of theparticles. The diffusiophoretic mobility (Γ_(p)) of the particles iscalculated using this location in the channel (x_(p)), and the zetapotential of the particles is derived from the diffusiophoreticmobility. In some embodiments, for example, particle zeta potential(ζ_(p)) is derived from diffusiophoretic mobility according to Equations(3)-(5):

$\begin{matrix}{\Gamma_{p} = {\frac{\epsilon}{2\eta}\left( \frac{k_{B}T}{Ze} \right)^{2}\frac{u_{o}}{1 - {u_{1}\text{/}\left( {u_{0}\kappa\; a} \right)}}}} & (3)\end{matrix}$where ∈ is the permittivity of the medium, η is the viscosity of themedium, k_(B) is the Boltzman constant, T is the absolute temperature,and e is the elementary charge. u₀ and u₁ are functions of zetapotential and when estimating k⁻¹, the concentration is assumed to be(c_(i)+c_(o))/2. Here,

$\begin{matrix}{u_{0} = {{2\left( \frac{D_{-} - D_{+}}{D_{-} + D_{+}} \right)\frac{{Ze}\;\zeta_{p}}{k_{B}T}} + {8\mspace{14mu}\ln\mspace{14mu}{\cosh\left( \frac{{Ze\zeta}_{p}}{k_{B}T} \right)}}}} & (4)\end{matrix}$where D⁻ and D₊ are, respectively, the diffusivities of cations andanions. u₁ is a series of exponential integrals where the lengthyexpressions can be found in Prieve et al., J Fluid Mech., 148:247-269,1984. For very large particles or vanishingly thin Debye layer (κα→∞),

$\begin{matrix}{\Gamma_{p} = {\frac{\epsilon}{\eta}\left( \frac{k_{B}T}{Ze} \right)^{2}\left( {{\left( \frac{D_{-} - D_{+}}{D_{-} + D_{+}} \right)\frac{{Ze}\;\zeta_{p}}{k_{B}T}} + {4\mspace{14mu}\ln\mspace{14mu}{\cosh\left( \frac{{Ze}\;\zeta_{p}}{4k_{B}T} \right)}}} \right)}} & (5)\end{matrix}$where ζ_(p) is particle zeta potential. As described herein, the solutegradient can be established, in some embodiments, by connecting thechannel with a second channel transporting fluid having a differingsolute concentration.

In another aspect, a method of determining particle zeta potentialcomprises providing at least one dead-end pore containing solute havinga first solute concentration and introducing a plurality of colloidalparticles into the dead end pore, the colloidal particles havingpositive diffusiophoretic mobility and a second solute concentrationless than the first solute concentration. The image intensity in thedead-end pore is measured, and the maximum colloidal density isdetermined based on the image intensity. Particle zeta potential isderived from the maximum colloidal density. In some embodiments, theimage intensity is measured after migration of the colloidal particlesin the dead-end pore reaches a quasi-steady state.

An overview of this zeta potentiometry technique is provided in FIGS.4A-D. Colloidal particles with solute concentration c_(o) are introducedto a dead-end pore containing higher solute concentration c_(i), asillustrated in FIG. 4A, leading to diffusiophoretic particle migrationinto/from the dead-end pore FIG. 4B. The direction of motion isdetermined by the particle surface charge and by the diffusivitydifference between anions and cations. The particle motion is alsoinfluenced by the presence of the wall surface charge, which inducesdiffusioosmosis that results in a circulating fluid flow. Duringmigration, the particles accumulate near the colloidal front since theparticle velocity u_(p) is proportional to the gradient of thelogarithmic solute concentration, i.e. u_(p)=Γ_(p)∇ln c, where Γ_(p) isthe particle diffusiophoretic mobility, which strongly depends on theparticle zeta potential ζ_(p) as shown in Equation 5 and FIG. 4B. Afterthe solute equilibrates across the pore, the colloidal distributionbecomes quasi-steady since the particle's diffusivity is negligiblecompared to that of the solute. The quasi-steady location of the maximumcolloidal density x_(m) ^(∞) is highly sensitive to ζ_(p). Thus, bylocating x_(m) ^(∞) from the intensity distribution, ζ_(p) can beobtained as provided in FIGS. 4C-D.

The foregoing principles are illustrated via the migration offluorescent colloidal particles (polystyrene, diameter=0.99 μm) into adead-end pore via NaCl gradient (c_(i)=10×10⁻³ M, c_(o)=0.1×10⁻³ M). Thepolystyrene particle migration is illustrated in FIG. 5A. NaCl is afavorable solute choice because it can generate significant LJP.Furthermore, the induced electrophoresis and chemiphoresis are in thesame direction under practical conditions, enabling relatively strongdiffusiophoresis. As mentioned, particles accumulate near the colloidalfront due to the logarithmic dependence on the solute gradient. Toidentify the location of the maximum colloidal density x_(m)(t), theparticle distribution can be inferred from the fluorescence intensitydistribution along the pore as shown in FIG. 5B. Over time, x_(m)asymptotically approaches its quasi-steady final position within a fewminutes (FIG. 5C). The location of the quasi-steady maximum colloiddensity x_(m) ^(∞) is defined as the peak location at three times thesolute diffusion time scale τ_(s), which in the present case is

$300\mspace{14mu} s\mspace{14mu}\left( {{\tau_{s} \approx \frac{l^{2}}{D_{s}} \approx {100\mspace{14mu} s}},} \right.$where l=400 μm is the pore length and D_(s)=1600 μm² s⁻¹ is the soluteambipolar diffusivity).

Although diffusiophoresis is a complex interfacial phenomenon occurringover nanometer length scales for individual particles, the macroscopicparticle dynamics can be predicted by solving advection-diffusionequations as follows. The transient particle dynamics in a dead-end porecan be modeled by solving advection-diffusion equations for the soluteand the particles. The equations for the solute c and the particles nare, respectively, given as:

$\begin{matrix}{\frac{\partial c}{\partial t} = {{D_{s}{\nabla^{2}c}} - {\nabla{\cdot \left( {u_{f}c} \right)}}}} & (6) \\{\frac{\partial n}{\partial t} = {{D_{p}{\nabla^{2}n}} - {\nabla{\cdot \left( {u_{p}n} \right)}}}} & (7)\end{matrix}$where u_(f) is the fluid velocity and u_(p)=u_(f)+u_(dp) is the particlevelocity, which is the sum of the fluid advection (u_(f)) and theparticle diffusiophoresis (u_(dp)). D_(s) is the ambipolar diffusivityof the solute and D_(p) is the particle diffusivity, which is obtainedfrom the Stokes-Einstein relation to obtain D_(p).

The length, width, and height of the dead-end pore are, L, w, and 2 h,respectively. The coordinates in length, width, and height are denotedas, respectively, x, y, and z, where the origin is located at the centerof the pore inlet. The boundary conditions at the inlet are c(x=0, y, z,t)=c_(o) and n(x=0, y, z, t)=1 while a no flux condition is imposed atthe channel walls. Initial conditions are c(x, y, z, 0)=c_(i) and n(x,y, z, 0)=0. Since the flow speed in the dead-end pore is due to thecirculating flow ϑ (10 μm/s), the Peclet number in the transversedirection to the pore axis of the solute migrating into a dead-end poreis far less than unity, indicating diffusion dominant transport. Thus,for the reduced order modeling (1D and 2D), the influence of flowadvection on the solute distribution is neglected and diffusion for thesolute transport is only considered. Due to the boundary condition, thesolution simplifies to c(x, y, z, t)=c(x, t).

The analytical solution to the transient solute concentration in adead-end pore is given by Equation (8):

$\begin{matrix}{{c\left( {x,t} \right)} = {c_{o} + {\left( {c_{i} - c_{o}} \right){\sum\limits_{n = 0}^{\infty}\;{b_{n}\mspace{14mu}{\sin\left( \frac{\lambda_{n}x}{L} \right)}e^{\lambda_{n}^{2}D_{s}t\text{/}L^{2}}}}}}} & (8)\end{matrix}$where b_(n)=2(1−1 cos λ_(n))/λ_(n) and λ_(n)=(2n+1)π/2. However, forfull 3D modeling, the influence of flow advection on the solutedistribution is accounted for, and the full advection diffusion equationis solved.

To account for the fluid advection induced by diffusioosmosis, aneffective wall slip velocity u_(w)=−Γ_(w)∇ln c is imposed along thechannel surface. For reduced order modeling (2D), the analyticalsolution to the flow profile in the length (x) and height (z) directionsis obtained by using the lubrication approximation with a zero netvolume flux constraint across the cross-section of the channel. Thevelocity field u_(f) (x, z)=(u_(f,x)(x, z), u_(f,z)(x, z) is given byEquations (9a) and (9b):

$\begin{matrix}{{u_{x}\left( {x,z} \right)} = {{- \frac{\Gamma_{w}}{2}}{\frac{d\;\ln\; c}{dx}\left\lbrack {{3\left( \frac{z}{h} \right)^{2}} - 1} \right\rbrack}}} & \left( {9a} \right) \\{{u_{z}\left( {x,z} \right)} = {\frac{\Gamma_{w}}{2}{\frac{d^{2}\ln\; c}{{dx}^{2}}\left\lbrack {z\left( {\left( \frac{z}{h} \right)^{2} - 1} \right)} \right\rbrack}}} & \left( {9b} \right)\end{matrix}$Using these equations for the flow advection, the advection-diffusionequation for the particles is numerically solved using MATLAB in thereduced order simulations.

By solving equations for both solute and particle suspension inside adead-end pore and considering the fluid advection due to thediffusioosmosis, the time-dependent particle distribution (FIGS. 5D and5E) including x_(m)(t) (FIG. 5F) can be predicted with excellentagreement with the experimental results illustrated in FIGS. 5a -c.

Due to the anisotropic geometry of the pore (length×width×height=400μm×48 μm×10 μm), reduced-order modeling gives excellent agreement withfull 3D numerical results. For example, 1D modeling, which onlyconsiders the length dimension, provides good agreement for x_(m) ^(∞)(see 1D curve in FIG. 5F), while 2D modeling, which accounts for thediffusioosmotic flow induced by the wall surface charge, alsosuccessfully predicts the transient dynamics (2D curve in FIG. 5f ).Since x_(m) ^(∞) is only considered when determining ζ_(p), 1D modelingis sufficient, offering computational efficiency and simplicity.

By solving the 1D advection-diffusion equation for the particles asdescribed herein, where advection is due only to diffusiophoresis,x_(m)(t) can be calculated for various particle zeta potentials as shownin FIG. 6. The results indicate that x_(m) ^(∞) is sensitive to ζ_(p),as shown in the inset of FIG. 6. Thus x_(m) ^(∞) is measuredexperimentally and ζ_(p) is extracted by comparison with one or moresimulations, including 1D simulations. Zeta potentials (ζ_(p,DP)) of avariety of particles were measured according to this solute gradientmethod. The results compared well with the zeta potentials (ζ_(ELS))measured by standard electrophoretic light scattering as evidenced inTable I.

TABLE I Zeta Potentials of various colloidal particles measured viasolute gradients and electrophoretic light scattering Particle 2a (μm)¹ζ_(p, DP) (mV) ζ_(p, ELS) (mV) Solution conditions² Polystyrene (BangsLab) 0.99 −80.1 ± 5.3 −67.5 ± 4.9 Polystyrene (Invitrogen) 1.1 −81.4 ±3.4 −79.2 ± 6.8 Polystyrene (Spherotech) 0.91 −87.2 ± 4.0 −72.5 ± 5.4Carboxylate-modified polystyrene 1.2 −72.1 ± 5.2 −74.7 ± 6.7Sulfate-modified polystyrene 0.53 −85.6 ± 3.9 −59.1 ± 4.9 Amine-modifiedpolystyrene 1.1  61.2 ± 4.4  58.8 ± 4.7 Decane 0.53 −88.7 ± 5.7 −104.3 ±8.2  50 mM NaCl, 1 mM SDS λ-DNA 0.29 −57.9 ± 6.4  −30.4 ± 10.9 pH = 8.3Unilamellar lipid vesicles 0.86  −54.2 ± 13.3  −89.5 ± 10.4 pH = 7.2, 1mM NaCl Non-fluorescent polystyrene 0.92 −84.5 ± 4.3 −68.8 ± 6.6Polymethyl methacrylate 1.3 −52.1 ± 6.6 −61.2 ± 7.8 ¹Measured by dynamiclight scattering ²c = (c_(i) + c_(o))/2 ≈ 5 mM NaCl and pH ≈ 6.0 unlessotherwise noted.

In view of the foregoing methods, zeta potentiometers are also describedherein. In some embodiments, a zeta potentiometer comprises at least oneflow channel, at least one light source for illuminating the flowchannel, and an imaging device positioned to observe the illuminatedflow channel. A sample storage location is adapted to provide a sampleto the at least one flow channel for analysis. FIG. 10 illustrates azeta potentiometer according to some embodiments. The zeta potentiometerin FIG. 10 employs a USB microscope as the imaging device and lightemitting diode (LED) backlight for channel illumination. The microscopeand LED are positioned opposite one another. Additionally, the samplestorage location is located above the channel, permitting sample flow tothe channel via hydrostatic pressure. The zeta potentiometer of FIG. 10can require small sample volumes, generally less than 100 μm, whileproviding fast analytical times, generally less than 5 minutes. In someembodiments, zeta potentiometers described herein do not employ anyexternal forces in the zeta potential analysis. Prior zetapotentiometers, for example, have employed external electric and/ormagnetic fields in the particle analysis. Electro-acoustic forces havealso been used in prior zeta potentiometers for particle analysis. Asshown herein, the described zeta potentiometers and associateddiffusiophoretic methods obviate the need for these external forces inparticle analysis.

In another aspect, methods of determining zeta potential of channelsurfaces and/or walls are described. In some embodiments, a method ofdetermining surface or wall zeta potential comprises providing at leastone dead-end pore containing a solute having a first soluteconcentration and introducing a plurality of colloidal particles havinga second solute concentration less than the first solute concentration.The plurality of colloidal particles migrate into the dead-end pore, andthe image intensity of the dead-end pore is measured prior to thecolloidal particle migration reaching a quasi-steady state. Thetransient peak position is determined from the image intensity, and zetapotential of the pore wall is determined from the transient peakposition. In some embodiments, wall zeta potential is determined byfitting the transient peak position to a power law curve, obtaining apower law exponent, and comparing the effective power law exponent toresults from a two-dimensional computer simulation.

Whereas the quasi-steady location of the maximum particle density x_(m)^(∞) was used to determine ζ_(p), the transient particle dynamics duringearly times contain information about wall zeta potential ζ_(w) due tothe presence of diffusioosmotic flow induced by the solute gradients.Although the net fluid flow in a dead-end pore is zero due toconfinement, nonzero local flow velocities exist because of balancebetween diffusioosmosis and induced pressure gradients driving oppositemotions. For example, the curved colloidal front of FIG. 5a furtherconfirms the contribution of pressure-driven flow. This flow balanceresults in circulating flow with magnitude proportional to |∇ln c| thatpropagates along the solute diffusion. For a negatively charged wallexposited to a solute gradient directed in the pore, the resulting flowdiverges from the center to the wall as illustrated in FIG. 7A. Thisflow pushes the particles, which have entered at the early stage, awayfrom the center toward the wall retarding the overall migration towardthe end of the pore (FIG. 7A).

Particle dynamics under such a circulating fluid flow are simulated byimposing a wall slip velocity, u_(w)=−Γ_(w)∇ln c, where Γ_(w) is thewall diffusiophoretic mobility, which is determined by ζ_(w). Due thechannel's narrow cross-section, it may be treated as a 2D systemconsidering the dimensions in the length (x) and height (z) directions,thereby reducing computational costs. The 2D approximation furtherallows analytical solutions for circulating fluid flow to be obtainedusing the lubrication approximation. Particle distributions calculatedfrom 2D simulations are presented in FIGS. 7B and 7C, showing theinfluence of this fluid flow on the particle dynamics. The presence ofthis circulating flow advects the particles toward the wall, retardingthe motion of x_(m)(t), especially at times early times, such as lessthan 60 s. However, the circulating flow is weakened over time, and thetransverse flow component exists only far from the inlet. Consequently,particles entering the in the late stage are hardly influenced by fluidadvection, ultimately resulting in similar x_(m) ^(∞) regardless ofζ_(w).

During this time-dependent behavior, at early times (<60 s) thetransient peak position deviates from diffusive ingress(x_(m)(t)˜t^(1/2)) in a power-law-like behavior (i.e., x_(m)(t)˜t^(β)),as shown in FIG. 7D. The effective power law exponent (β) is empiricallyobserved to be sensitive to both ζ_(p) and ζ_(w) since the transientdynamics are a consequence of interplay between the particlediffusiophoresis and the diffusiophoretic fluid advection. The exponentβ is given the inset of FIG. 7D for a wide range of ζ_(p) and ζ_(w) andcan be used to determine ζ_(w) from a known ζ_(p).

A prerequisite for measuring ζ_(w) using this method is that Γ_(p) mustbe larger than Γ_(w). If Γ_(w)≥Γ_(p), the constant particle inletcondition for the simulations becomes invalid, since the number ofparticles leaving the pore due to the circulating flow is greater thanthe number entering the pore.

This method is demonstrated by performing experiments with polystyreneparticles in bare and plasma-treated poly-(dimethylsiloxane) (PDMS)channels (FIG. 7E). Plasma treatment significantly increases the surfacecharge, thereby increasing ζ_(w). As predicted, the plasma-treatedchannel exhibits much slower migration in the early stage compared tothe untreated surface, although x_(m) ^(∞) is similar for both cases.ζ_(w) was determined by obtaining β (FIG. 7F) and comparing tosimulation results (inset of FIG. 7f ). The results are approximately−55 mV for the untreated −72 mV for the plasma-treated PDMS surfaces,which are in good agreement with prior literature values.

In another aspect, methods of determining the zeta potential of channelwalls or surfaces via pressure measurements are described. A method ofdetermining zeta potential of channel walls or surfaces, in someembodiments, comprises establishing a solute concentration gradient toinduce a wall slip boundary condition in the channel. The pressure dropalong the channel is measured, and channel wall diffusiophoreticmobility of the slip boundary condition is derived from the measuredpressure drop. The zeta potential of the channel walls or surfaces isderived from this wall diffusiophoretic mobility. In some embodiments,for example, wall diffusiophoretic mobility is derived from a relationbetween the measured pressure drop and the wall slip velocity of theboundary condition.

The solute concentration gradient can be established by any meansconsistent with the methods described herein. In some embodiments, forexample, the solute gradient is established by coupling each channel endto a larger channel, wherein the larger channels carry soluteconcentrations at different speeds. FIGS. 8A and 8B illustrate such asetup wherein ends of a channel 80 are coupled to larger main channels(Channel 1 and Channel 2). In the embodiment of FIGS. 8a-b , Channel 1carries a nondimensional solute concentration of c=1 at a mean speed ofat a mean speed of Ū_(main, 1) and Channel 2 carries a nondimensionalsolute concentration of c=β at a mean speed of Ū_(main, 2). Dynamicswithin the pore are established by driving the main flows in Channels 1and 2 at different speeds. For example, with Ū_(main, 1)>Ū_(main, 2), apressure gradient along the channel 80 will drive flow through thechannel 80 at a mean speed of Ū>0. With steady inlet/outlet conditions,a steady-state solute concentration gradient will develop within thechannel 80 on a timescale of L²/D_(s), where for low Reynolds numbersthe flow is quasi-steady with respect to the solute dynamics, andwherein L is channel 80 length and D_(s) is solute diffusivity. As thissolute gradient develops, slip boundary conditions at the channel 80walls drive recirculating secondary flows through diffusioosmosis, whichcause deviations in the pressure gradient along the channel 80. Thispressure gradient is directly related to the zeta potential of thechannel 80 walls, making possible the use of such a system to performzeta potentiometry of surfaces using fluid measurements. FIG. 8b is amagnified view of the channel 80 of dimensions 2 h₁×2 h₂ wherein thesolid arrows denote the direction of flow.

The equations governing the coupled fluid/solute dynamic include theNavier-Stokes and continuity equations, as well as theadvection-diffusion equation for the dissolved solute dynamics.Analytical solutions can be achieved via the lubrication approximationfor the case of long narrow channels. The unique feature thatdifferentiates methods and systems described herein, including thatillustrated in FIGS. 8a and 8b , from a traditional pressure-drivenPoiseuille flow calculation is the addition of wall slip boundaryconditions on the pore walls due to the action of diffusioosmosis thatis driven by local solute concentration gradients. The slip boundaryconditions result in deviations of the pressure gradient within thechannel from the Poiseuille flow case with no-slip boundaries. As shownbelow, zeta potential of the channel surfaces can be calculated directlyfrom the total pressure drop along the channel.

The pressure drop along the channel Δp=p(1)−p(0) is given by Equation(10):

$\begin{matrix}{{\Delta\; p} = {\frac{3}{{3C^{*}} - 1}\left( {1 + {\frac{\Gamma_{w}}{L\overset{\_}{U}}\ln\mspace{14mu}\beta}} \right)}} & (10)\end{matrix}$Therefore, the pressure drop is uniquely specified by the soluteconcentration ratio β, the channel aspect ratio h₁/h₂ (through C*), andthe dimensionless diffusioosmotic mobility of the channel walls

$\frac{\Gamma_{w}}{LU},$where Γ_(w) is channel wall or channel surface diffusioosmotic mobility.For a typical system, h₁/h₂ and β will be given system designparameters. Equation 10 then directly relates the diffusioosmoticmobility of the channel walls with the total pressure drop Δp along thelength of the channel, which may be measured. Therefore, in practice,the measurement of a single pressure drop in a microfluidic system issufficient to determine wall diffusioosmotic mobility Γ_(w), whereinzeta potential of the channel walls or channel surfaces can be derivedfrom Γ_(w).

Zeta potential (ζ) can be proportional to the logarithm of the soluteconcentration for the case of symmetric electrolytes with a valence ofone for a wide range of solute concentrations. Specifically, if thecations do not show specific adsorption, the zeta potential is given asζ=−a ₁ ln cwhere a₁ is a constant of proportionality. Then neglecting correctionsdue to finite Debye layer effects, the diffusioosmotic mobility can bewritten as Equation (11):

$\begin{matrix}{\Gamma_{w} = {\frac{\epsilon}{\mu}{\left( \frac{k_{B}T}{Ze} \right)^{2}\left\lbrack {{\left( \frac{D_{+} - D_{-}}{D_{+} + D_{-}} \right)\frac{{Ze}\;\zeta}{k_{B}T}} + {4\mspace{14mu}\ln\mspace{14mu}{\cosh\left( \frac{{Ze}\;\zeta}{4k_{B}T} \right)}}} \right\rbrack}}} & (11)\end{matrix}$where ∈ is the permittivity of the medium, μ is the dynamic viscosity ofthe medium, k_(B) is the Boltzman constant, T is the absolutetemperature, e is the elementary charge, Z is the valence of the solute,D₊ and D⁻ are the diffusivity of cations and anions respectively, and ζis zeta potential of the channel walls or surfaces.

FIG. 9 illustrates a system design for measuring zeta potential ofchannel walls or surfaces according to some embodiments. As illustratedin FIG. 9, the channel or pore of interest is connected to two mainchannels as in FIG. 8. Notably, the pore extends through the two mainchannels for connection to pressure measurement ports. The system alsoprovides holes or ports for connecting the main channels to flow pumps.

Channels employed in one or more of the methods described herein canhave any dimensions not inconsistent with the objectives of the presentinvention. In some embodiments, channels are of dimensions suitable formicrofluidic analysis. Additionally, fluid advective velocities in thechannels can be controlled with one or more pumps. As detailed herein,fluid advective velocity can include a diffusioosmotic component orcontribution, which is a function of at least channel wall zetapotential. Moreover, diffusioosmotic velocity is fluid velocity at thechannel wall and is incorporated into fluid advective velocity alongwith the pressure induced flow. In some embodiments, fluids employed inthe present methods are one or more biological fluids. In otherembodiments, the fluids are non-biological fluids.

Particle manipulation and/or separation methods and systems describedherein can be employed in a variety of applications including, but notlimited to, fluid filtration, such as water filtration, particlesorting, separation, and focusing, and diagnostic and measurementapplications.

Various embodiments of the invention have been described in fulfillmentof the various objectives of the invention. It should be recognized thatthese embodiments are merely illustrative of the principles of thepresent invention. Numerous modifications and adaptations thereof willbe readily apparent to those skilled in the art without departing fromthe spirit and scope of the invention.

The invention claimed is:
 1. A method of manipulating particle motioncomprising: introducing a fluid into a channel, the fluid comprisingparticles; and driving particle accumulation to a preselected locationin the channel by setting advective velocity of the fluid to offsetdiffusiophoretic velocity of the particles at the preselected location.2. The method of claim 1, wherein diffusiophoretic velocity of theparticles is a function of particle size, particle surface charge,strength of a solute gradient in the fluid or various combinationsthereof.
 3. The method of claim 2, wherein the solute gradient isestablished by connecting the channel with a second channel transportingfluid having a differing solute concentration.
 4. The method of claim 1further comprising characterizing one or more properties of theaccumulated particles.
 5. The method of claim 1 further comprisingremoving the particles from the channel.
 6. The method of claim 1,wherein non-accumulated particles in the fluid are passed out of thechannel.
 7. The method of claim 1, wherein the particles comprise one ormore biomolecular species.
 8. The method of claim 7, wherein thebiomolecular species comprise small-molecule drugs, nucleic acids,proteins, viruses or mixtures thereof.
 9. The method of claim 1, whereinthe fluid advective velocity comprises a pressure contribution and adiffusioosmotic wall slip contribution.
 10. A method of particleseparation comprising: introducing a fluid into a channel, the fluidcomprising a mixture of particle species; and separating the particlespecies in the fluid by driving accumulation of the particle species topreselected locations in the channel via setting advective velocity ofthe fluid to offset diffusiophoretic velocity of a particle species ateach of the preselected locations.
 11. The method of claim 10, whereindiffusiophoretic velocity of each particle species is a function ofparticle size, particle surface charge, strength of a solute gradient inthe fluid or various combinations thereof.
 12. The method of claim 11,wherein the solute gradient is established by connecting the channelwith a second channel transporting fluid having a differing soluteconcentration.
 13. The method of claim 10 further comprisingcharacterizing the particle species accumulated at each of thepreselected locations.
 14. The method of claim 10 further comprisingremoving the separated particle species from the channel.
 15. The methodof claim 10, wherein the particles species comprise various biomolecularspecies.
 16. The method of claim 10, wherein the fluid advectivevelocity comprises a pressure contribution and a diffusioosmotic wallslip contribution.
 17. A method of particle analysis comprising:introducing a fluid sample into a channel; determining the presence ofanalyte particles in the fluid sample by driving accumulation of theanalyte particles to a preselected location in the channel via settingadvective velocity of the fluid sample to offset diffusiophoreticvelocity of the analyte particles at the preselected location; anddetecting the presence of the analyte particles at the preselectedlocation.
 18. The method of claim 17, wherein diffusiophoretic velocityof the analyte particles is a function of particle size, particlesurface charge, strength of a solute gradient in the fluid or variouscombinations thereof.
 19. The method of claim 17 further comprisingcharacterizing one or more properties of the accumulated analyteparticles.
 20. The method of claim 17 further comprising removing theanalyte particles from the channel.
 21. The method of claim 17, whereinthe non-accumulated particles in the fluid are passed out of thechannel.
 22. The method of claim 17, wherein the fluid advectivevelocity comprises a pressure contribution and a diffusioosmotic wallslip contribution.
 23. A method of particle analysis comprising:introducing a fluid sample into a channel; determining the presence of aplurality of analyte particle species in the fluid sample by drivingaccumulation of the analyte particle species to preselected locations inthe channel via setting advective velocity of the fluid to offsetdiffusiophoretic velocity of an analyte particle species at each of thepreselected locations; and detecting the presence of the analyteparticle species at each of the preselected locations.
 24. The method ofclaim 23, where diffusiophoretic velocity of the each analyte species isa function of particle size, particle surface charge, strength of asolute gradient in the fluid or various combinations thereof.
 25. Themethod of claim 23 further comprising selectively removing one or moreof the analyte species from the channel.
 26. The method of claim 23further comprising characterizing one or more properties of theseparated analyte species.
 27. The method of claim 23, wherein theanalyte species comprise biomolecular species.
 28. The method of claim24, wherein the biomolecular species comprise small-molecule drugs,nucleic acids, proteins and/or viruses.
 29. A method of determiningparticle zeta potential comprising: introducing a fluid into a channel,the fluid having an advective velocity and solute concentrationgradient; introducing particles into the fluid, and accumulating theparticles at a location in the channel where the advective velocity ofthe fluid is offset by diffusiophoretic velocity of the particles;calculating the diffusiophoretic mobility of the particles from thelocation in the channel; and deriving zeta potential of the particlesfrom the calculated diffusiophoretic mobility.
 30. The method of claim29, wherein the solute gradient is established by connecting the channelwith a second channel transporting fluid having a differing soluteconcentration.